Vascular elastance

ABSTRACT

A device includes a balloon and an interface. The balloon has an outer surface and a central lumen aligned on a longitudinal axis. The balloon is configured to receive a compressible fluid. The interface is coupled to the outer surface and has an external surface configured to bond with a tissue.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional of U.S. patent application Ser. No.13/701,721, filed Dec. 3, 2012, now U.S. Pat. No. 9,987,153, which is anational phase of International PCT Patent Application Serial No.PCT/US2011/038558, filed May 31, 2011, which claims priority to U.S.Provisional Patent Application Ser. No. 61/352,774, filed Jun. 8, 2010,the entire contents of each of which are incorporated herein byreference.

BACKGROUND OF THE INVENTION

Pulmonary Hypertension (PH) is a condition characterized by elevatedblood pressure in the pulmonary circulation. It can be caused bymultiple diseases and if not controlled, leads to right heart failureand death. Depending on the form of the disease, afflicted individualscan have poor quality of life and a very poor prognosis. According toone authority, median survival time for untreated idiopathic pulmonaryarterial hypertension in 2002 was 2.8 years. PH can be defined as a meanblood pressure in the pulmonary artery greater than 25 mmHg at rest.

SUMMARY

A healthy artery is an elastic vascular structure that can deform whenacted on by mechanical forces. With some diseases, such asarteriosclerosis and hypertension, an artery becomes less compliant thannormal. This reduction in compliance results in a relatively highpulsatile pressure in the artery for a given stroke volume. A reductionin arterial compliance increases the hydraulic loading on the heart andincreases the amount of energy lost in the pulsatile components. Inlight of the pulsatile component loading on the right heart, a decreasein arterial compliance can be problematic.

An example of the present subject matter is configured for treatinghypertension of the systemic or pulmonary circulations. In hypertension,the relatively low compliance of the arteries can contribute to highpeak arterial pressures. The high peak arterial pressure, in turn,causes high peak ventricular wall stress and energy expenditure. Overtime, this increases cardiac burden can lead to heart failure, andultimately, death.

An example of the present subject matter is configured to reduce thepulsatile stiffness component of arterial elastance and as aconsequence, improve systemic arterial elastance with the effect ofminimizing the afterload on the right heart.

An example of the present subject matter is configured to reduce thepulsatile arterial elastance. In one example, a compressible device isimplanted within the blood vessel. The device has a volume (sometimesreferred to as a compressible volume) that changes when subjected topressure within the vessel. For instance, a pressure change within thevessel can cause the device to compress from a first volume to a secondvolume and thereby provide a reduction in vessel elastance.

In one example, a device includes both a rigid structure and acompressible volume that is configured to encircle an artery. Thecompressible volume portion can compress during vessel distension. Assuch, the device functions as a spring. In one example, the device iscoupled to a wall of the vessel and is located external to the vessel orpartially external to the vessel. In one example, the device isconfigured for placement within the muscular vessel wall.

In one example, an energy storage device is coupled to a vessel. Thatdevice is configured to absorb energy from the system at a first timeand return energy to the system during a second time. The energy storagedevice, in one example, includes a fluidic accumulator having a dynamicelement. The dynamic element can include an elastic membrane or apiston. Examples of the present subject matter are suitable fortreatment related to heart failure, general hypertension or pulmonaryhypertension.

These and other examples and aspects of the present devices and methodsare set forth in the following Detailed Description. This Summary isintended to provide an overview of the subject matter of the presentpatent document. It is not intended to provide an exclusive orexhaustive explanation of the present invention. The DetailedDescription is included to provide further information about the subjectmatter of the present patent document.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings, which are not necessarily drawn to scale, like numeralsmay describe similar components in different views. Like numerals havingdifferent letter suffixes may represent different instances of similarcomponents. The drawings illustrate generally, by way of example, butnot by way of limitation, various embodiments discussed in the presentdocument.

FIG. 1 illustrates a transverse view of a device according to oneexample.

FIG. 2 illustrates a sagittal view of a device according to one example.

FIG. 3 illustrates a sagittal view of a device having multiple segmentsaccording to one example.

FIG. 4 illustrates a transverse view of a device having multiplesegments according to one example.

FIG. 5 illustrates a sagittal view of a device having multiple segmentsaccording to one example.

FIG. 6 illustrates a lateral cross sectional view of a device having anextra-vascular compliant member according to one example.

FIG. 7 illustrates a lateral cross sectional view of one embodiment ofan extra-vascular compliant member according to one example.

FIG. 8 illustrates a lateral cross sectional view of one embodiment ofan extra-vascular compliant member according to one example.

FIG. 9 illustrates an elevation view of a device according to oneexample.

FIG. 10 illustrates a top view of a device according to one example.

FIG. 11 illustrates a sagittal view of a fenestrated device according toone example.

FIG. 12 illustrates a transverse view of a fenestrated device accordingto one example.

FIG. 13 illustrates a lateral view of an embedded device according toone example.

FIG. 14 illustrates a transverse view of an embedded device according toone example.

FIGS. 15 and 18 illustrate lateral views of a bi-modal device accordingto one example.

FIG. 17 illustrates a view of a device according to one example.

DETAILED DESCRIPTION OF THE INVENTION

In pulmonary hypertension, the structure and function of both thepulmonary artery and right ventricle are altered. Right ventricularperformance is influenced by arterial load and arterial properties are,in turn, influenced by right ventricular performance. This interaction,called arterial-ventricular coupling, plays a role in determiningcardiovascular performance and cardiac energetics.

Elastance can be expressed as a change in pressure for a given change involume, E=ΔP/ΔV. For the pulmonary artery, the Effective ArterialElastance, E_(PA), represents the total arterial load imposed on theright ventricle (afterload). It is proportional to the sum of the steadystate resistive component (Cardiac Output Pulmonary Vascularresistance)+the pulsatile, stiffness component (End SystolicPressure-Mean Arterial Pressure/Stroke Volume)+the load generated byreflected waves.

Afterload is caused by the dynamic interplay between steady stateresistance, dynamic stiffness and wave reflections. In PulmonaryArterial Hypertension, both the steady state and the pulsatilecomponents of afterload are increased. In addition, the alteredPulmonary Arterial stiffness and right ventricular timing cause thereflected waves to significantly contribute to ventricular afterload,whereas in a normal individual reflected waves have a much smallereffect.

Compliance is a measure of the ability of an elastic body to accommodatedeformation. When considering a closed volume, compliance is defined asthe ratio of the change of internal volume to the change in internalpressure due to an externally applied force. Mathematically, compliancecan be expressed as C=ΔV/ΔP and is the multiplicative inverse (orreciprocal) of elastance.

The right and left ventricles of the heart pump blood into the pulmonaryartery and aorta respectively. As the heart undergoes systole anddiastole, pulsatile flow is generated such that localized periodicpressure rises and falls about the mean arterial pressure. A timeresponse of blood pressure at a particular location along the arteryexhibits a periodic variation of pressure levels about the mean that iscorrelated with systole and diastole.

In addition to the pulmonary artery, examples of the present subjectmatter can be used to increase the compliance of other fluid-carryingorgans. As used herein, an organ includes tissue having a particularfunction. An organ can be a component of an anatomical system such asvessel in a circulatory system. One example of the present subjectmatter is configured to increase the compliance of a vessel (such as anartery, a capillary, or a vein) or other hollow organ. A hollow organcan include a visceral organ having a hollow tube or pouch (such as thestomach or intestine) or that includes a cavity (such as the heart orurinary bladder). For instance, one example is configured for placementin a component of the urinary system and may be suitable for treatmentof incontinence.

An example of the present subject matter includes an energy absorbingdevice configured to respond to fluidic pressure changes within anorgan. As such, the device provides a smoothing function as to changesin the fluid pressure. For example, the maximum pressure is reduced andthe minimum pressure is raised. The change in pressure dynamics can alsoinclude a shift in the mean pressure level within the organ.

Consider one example in which the present subject matter is configuredfor placement in an artery of a vascular system. In such an example, anenergy storage device is coupled to the artery to increase tissuecompliance. The energy storage device can include a compliant memberlocated within the artery, a compliant member coupled to the artery by afluidic channel, or a compliant member wholly or fully embedded in awall of the artery. In one example, the energy storage device caninclude a fluidic accumulator. In another example, the energy storagedevice can include a compliant member having a flexible membrane thatsurrounds a compliant volume.

A flexible membrane can include a structure whose stiffness can bechanged. The stiffness can be changed by changing pressure within thecompliant volume by various means including direct variation of internalpressures such as injection of gas through a catheter or needle,transfer of materiel from a small volume of relatively high pressure toa larger volume of relatively lower pressure, conversion of materialfrom solid to gas, conversion of material from liquid to gas or theaddition of compliant materials such as gas, foam, or hydro-gel.

The stiffness of the flexible membrane can also be changed by selectionof the membrane material or selection of the membrane thickness. Inaddition, the stiffness can be changed by selection of the membranegeometry. In one example, the stiffness is remotely adjustable using anexternal energy source such as ultrasound, electromagnetic waves, ormagnetic field variations such as an electrically induced vaporizer.

A compliant volume is a structure substantially bounded on all sides bysurfaces that can include, among others, a flexible membrane or apiston. The compliance of the compliant volume can be adjusted bychanging the pressure within the compliant volume by various meansincluding direct variation of internal pressures or the addition ofcompliant materials such as gas, foam, or hydro-gel. In addition,material selection and thickness can be used to tailor a particularcompliant volume. Adjustments can also be made in the geometry of thecompliant volume or by using an induced vaporizer or gas generator.

Differential pressure is the instantaneous variation of pressure betweenthat experienced in the bodily lumen and that experienced in thecompliant volume defined by the compliant body. A positive differentialpressure indicates lumen pressure exceeds compliant volume pressure. Anegative differential pressure indicates compliant volume pressureexceeds lumen pressure.

An example of the present subject matter can be held in place, oranchored, by various structures. The present subject matter is anchoredto reduce the risk presented by an embolized structure. For example, adevice can be anchored by a suture, a stent, a friction fit, expansionto fill a hollow or vascular space, a hook mechanism, vascularendothelial in-growth, a barb mechanism, a rivet, compression exerted byadjacent tissue, or a magnet.

An example of the present subject matter can be delivered to theinstallation site by various procedures, including a surgical procedureor a percutaneous procedure. For example, general surgery, percutaneoustranscatheter surgery, thorascopically, and intra or extra vascularplacement can be used. A minimally invasive surgical procedure can beused to install a device. A percutaneous installation procedure caninclude using a needle, an introducer guide wire, an introducer sheath,and a catheter. The catheter can also be used to inflate or pressurizethe device after installation. Such methods and tools can also be usedfor device removal or to reposition a device.

In one example, the device is fabricated of a material that isbiocompatible. In addition, one example includes a biologicallyabsorbable material. Other materials can also be used. For example, amaterial that assists in the growth of endothelial cells on a surfacecan be used for various components. In one example, a component isfabricated of a material having a smooth, low friction surface thatfacilitates implantation or removal.

Device fabrication can include manufacturing a balloon. In addition,molded or formed materials, such as sheet goods, can be used in thefabrication of such a device. A fatigue resistant polymer havingsufficient flexibility can be used for a membrane. In one example, amembrane is fabricated using a sputter-coating (diffusion layer) tolimit gas pass-through.

FIGS. 1 and 2 illustrate transverse and sagittal views, respectively, ofdevice 100 according to one example. In the example illustrated, device100 includes interface 110 and compliant body 115. Interface 110includes a stent-like anchoring device and is configured, in thisexample, for placement within a blood vessel, such as artery 105.Channel 120 is a lumen aligned with artery 105 and carries blood.

Interface 110 can include a metal or non-metal mesh selected to promotebonding with the endothelium layer. The endothelium is a thin layer ofcells that line the interior of blood vessels, thus forming an interfacebetween circulating blood lumen and the vessel wall.

In one example, interface 110 forms a fluid-tight joint with the innersurface of the walls of artery 105. In one example, interface 110 isloosely fitted within artery 105 and blood, or other fluid, is allowedto pass between compliant body 115 and the inner surface of the walls ofartery 105. Device 100 can be retained in artery 105 by an interferencefit with the vessel wall.

Compliant body 115 presents a compliant volume. The undeformed shape ofthe compliant volume is defined by a resilient or flexible membrane ofcompliant body 115. Compliant body 115 can readily deform to assume avariety of shapes including, but not limited to, cylindrical,ellipsoidal, polygonal cross-sections with mitered, concave, or convexfeatures along the length of the central compliant volume. In oneexample, compliant body 115 includes a toroidal cylindrical shape of alength and a diameter corresponding to the compliant volume.

Device 100 is held in fixed alignment relative to the vasculature usingan anchor structure. In the example shown, the outer surface ofcompliant body 115 is fastened to interface 110. Interface 110 includesa stent-like component which expands on deployment to intimately contactthe wall of artery 105 to reduce embolization of the device 100. In oneexample, device 100 is located within the lumen of artery 105 andinterface 110 allows device 100 to be suspended within the lumen.

In operation, the device 100 is located within the vasculature and isexposed to pulsatile pressure loads. Under positive differentialpressure, blood flowing in artery 105 exerts a force against device 100and deforms the compliant body 115 such that an equivalent volume ofblood occupies the space of the compliant body 115. Under negativedifferential pressure, the compliant body 115 returns to the original,undeformed position.

FIG. 3 illustrates a sagittal cross sectional view of an example havinga plurality of annular compliant bodies 115 coupled to a commoninterface 110 disposed in artery 105. In this example, each compliantbody 115 operates independently of any other compliant body 115.

The number of individual compliant bodies 115 is not limited and isselectable according to the compliancy requirements of a particularapplication.

FIGS. 4 and 5 illustrate views of an example having a plurality oflongitudinal compliant bodies 415 and interface 110 disposed in artery105. The compliant bodies 415 in this example are distributed about theinterior of the artery and each has a rounded linear profile. Theparticular profile is selected to provide a variable volume region thatis distributed in a manner to maintain uniform blood flow within a largeportion of the lumen. A variety of profiles are contemplated, includingcylindrical, ellipsoidal, polygonal cross-sections with mitered,concave, or convex features along the length of each individualcompliant body 415.

The examples shown includes a common interface 110, however, a pluralityof individual segments of interface 110 can also be used.

FIG. 6 illustrates a lateral cross section view of device 600 accordingto one example. Device 600 includes compliant body 620 configured tosurround the periphery of artery 105. Compliant body 620 can have ashape defined by a flexible membrane (or balloon) and can have a varietyof shapes, including cylindrical, ellipsoidal, polygonal cross-sectionswith mitered, concave, or convex features along the length of thecompliant body 620. In the example shown, compliant body 620 includes aflexible membrane having a toroidal shape with a circularcross-sectional area and a length selected to encompass a volumesufficient to provide a therapeutic effect. Compliant body 620 caninclude a sheet of material suitable for wrapping around artery 105. Inthe example shown, compliant body 620 is wrapped and joined in the areanear joint 615.

Shell 610 surrounds the outer surface of compliant body 620. In theexample illustrated, shell 610 is wrapped around artery 105 and isjoined and secured at joint 615. Shell 610 provides a rigid frame orstructure and forms a self-reacted structure to prevent expansion ofcompliant body 620 beyond the periphery of the shell 610. In oneexample, the compliant body 620 is connected to the inner periphery ofshell 610. In one example, compliant body 620 and shell 610 are tubularstructures.

Shell 610 and compliant body 620 are connected in a manner to bring theinner periphery of the compliant body 620 into intimate contact with theouter periphery of artery 105.

Device 600 is secured to the vasculature with an anchor structure. Inthis example, since the compliant body 620 is in intimate contact withthe outer periphery of artery 105, a friction force is generated byjoint 615.

In operation, as the artery 105 distends during systole, the compliantbody 600 is exposed to pulsatile pressure loads creating a positivedifferential pressure. As the compliant body 600 is bounded about theouter periphery by shell 610, a positive differential pressure deformsthe compliant body 620 such that an equivalent volume of blood occupiesthe space of the compliant volume. Under negative differential pressure,compliant body 620 returns to the original undeformed position.

FIGS. 7 and 8 illustrate lateral cross sectional views of examples ofextra-vascular devices 700 and 800, respectively. In FIG. 7, device 700includes compliant volume 725 defined by a flexible membrane 715 and thewalls of device 700. The undeformed shape of the compliant volume canassume many shapes including, but not limited to, cylindrical,ellipsoidal, polygonal volumes with mitered, concave or convex featuresalong the length of the compliant volume. In this example, membrane 715has a flat, circular cross-sectional area and a length specified toencompass a volume sufficient to realize the desired therapeutic effect.In one example, membrane 715 is concave with respect to the compliantvolume.

Membrane 715 is located at aperture 710 and proxies a fluid-tight jointbetween 725 and the lumen of artery 105.

Device 700 is secured to the vasculature or surrounding tissue withfeature 720 or by other anchor structure. In the example shown, feature720 can include a suture however an adhesive or endothelial growth canalso provide an anchor. In this example, feature 720 is disposed on anexternal surface of artery 105.

In the operation, membrane 715 is exposed to pulsatile pressure loads inartery 105. Under positive differential pressure, blood flowing inartery 105 presses against the device 700 and deforms membrane 715 suchthat an equivalent volume of blood occupies the space of the compliantvolume. Under negative differential pressure, membrane 715 returns tothe original, undeformed position.

FIG. 8 illustrates an example in which device 800 includes a wallfabricated of a resilient material. Volume 825 has a variable volumebased on deflection of device 800 and position of membrane 815. Membrane815 is located at aperture 810. Feature 820 provides an anchoringstructure for affixing device 800 to artery 105. Feature 820 is disposedon an interior surface of artery 105. Device 800 assumes a generallybulbous shape with increasing pressure within artery 105.

FIGS. 9 and 10 illustrate device 900 having compliant body 920 and acentral compliant volume. FIG. 9 illustrates a front view and FIG. 10illustrates a top view. Device 900 is configured for placement withinthe branches of a main pulmonary artery (left and right). The undeformedshape of the central compliant volume is defined by a flexible membraneof body 920 that can assume many shapes including, nut not limited to,cylindrical, ellipsoidal, polygonal cross-sections with mitered,concave, or convex features along the length of the central compliantvolume. In this example, the flexible membrane forms a triangular volumeshape of a given length, base and height based on the central compliantvolume required for specific patient therapeutic requirements. In oneexample, one or more surfaces defined by the flexible membrane can be ofa different material with different stiffness and compliance properties.

Device 900 is secured within the blood vessel lumen with an anchorstructure. In this example, compliant body 920 is secured within bloodvessel lumen by a scaffold-like structure for placement near abifurcating vasculature anatomy. The scaffold-like structure includesstructural rings 910 and 915 attached to the support structure base 930at angles from 0 to 180 degrees as defined by an included angle measuredfrom a surface of the compliant body 920 to the planar surface ofstructural ring 910 or 915. Structural rings 910 and 915 can be locatedin or near the bifurcating vasculature anatomy, respectively, to anchorthe compliant body 920 at, or near, the bifurcation and are distributedaround the periphery of the support structure base 930 at a location tolocate structural rings 910 and 915 in the bifurcating vessels.

A diameter of rings 910 and 915 are a function of the diameter of thebifurcating vessels.

The support member 940 attaches to the support structure base 930 atappropriate locations along the periphery of the support structure base930 at a first end and to the lower support base 950 at appropriatelocations along the periphery of the lower support base 950 at thesecond end. The support member 940 and lower support base 950 arelocated in the primary vessel with support member 940 of a length toprovide the support structure base 930 with sufficient lateral supportto prevent embolization during systolic/diastolic heart function. Thediameter of lower support base 950 is selectable based on the anatomy ofthe particular patient into which the device will be inserted. Supportstructures 910, 915, 930, 940, and 950 are made of bio-compatible, shapememory alloy materials such nitinol.

In one example, device 900 is secured in position to allow the compliantbody 920 to be suspended within the blood vessel lumen.

In the operation, the compliant body 920 is exposes to pulsatilepressure loads in the blood vessel lumen. Under positive differentialpressure, blood flowing in the vessel lumen presses against the device900 and deforms the flexible membrane such that an equivalent volume ofblood occupies the space of the compliant volume. Under negativedifferential pressure, the flexible membrane returns to the original,undeformed position.

Device 900 provides increased vessel compliance and is configured todivert acoustic waves to reduce reflections and the effects ofafterloading.

FIGS. 11 and 12 illustrate a sagittal and transverse cross sectionalviews, respectively, of fenestrated device 1100 in artery 105. Device1100 includes compliant body 1110 in the form of a toroidal balloon. Aplurality of fenestrations 1115 are provided in the balloon and theperimeter of each fenestration 1115 is bonded to retain a closed volumewithin compliant body 1110. The bonded perimeters of each fenestration1115 presents an appearance similar to that of quilt stitching. Theaperture of each fenestration 1115 provides a region where endotheliumcells on the inner walls of artery 105 infuse and bond with thecompliant body 1110, thus holding device 1100 at a fixed location withinartery 105. Between adjacent fenestrations 1115, the balloon walls areseparated by a distance that is maximal at the midway point between thefenestrations and tapers uniformly to the bonded joint at the perimeterof the fenestrations. Fenestrations 1115 are depicted as oval shapes andin various examples, can include longitudinal slits or rectangularwindows.

When inflated with a pre-charge of gas, the portions of compliant body1110 located between adjacent fenestrations may take on a facetedappearance in which the portions or compliant body 1110 that are bondedto the inner wall of artery 105 are joined by relatively straightsegments of inflated balloon material. In FIG. 12, the cell growthbetween the compliant body 1110 and the wall of artery 105 is not shown.The web of material between the fenestrations can be biased to enlargethe bore of the lumen by selection of suitable materials for the innerand outer portions of the toroidal balloon, by selection of materialthickness. In addition, an internal structure can be molded within theballoon to provide a specified bore. Furthermore, an installation toolhaving a stent-like support structure can be used to temporarily bringthe web into contact with the vessel wall and thereby promoteendothelial cell growth.

The number of fenestrations and the arrangement of fenestrations andballoon material can be tailored to provide a larger or smaller numberof contact points with the arterial wall. In addition, adjacent balloonsegments (defined between fenestrations) can be independent orcontinuous.

The compliant volume of device 1100 is defined by the toroidal balloonand lies between the fenestrations. The undeformed shape of device 1100is defined by a flexible membrane of compliant body 1110 into which aquilted pattern of holes 1115 is fenestrated to allow endothelial tissuegrowth over the surface of the flexible membrane. The undeformed shapeof the compliant volume can assume many shapes including, but notlimited to, cylindrical, ellipsoidal, polygonal cross-sections withmitered, concave or convex features along the lengths of the compliantvolume. In this example, the flexible membrane is formed into a toroidalcylindrical shape of a length and diameter based on the compliant volumerequired for specific patient therapeutic requirements. In one example,device 1100 is separated into individual compliant bodies 1110 of alength less than the total length required to achieve specific patienttherapeutic requirements and deployed into the artery 105 to convenientlocations as required to realize the compliant volume required forpatient therapeutic requirements.

Device 1100 is secured to the vasculature by an anchor structure orfeature. In the example shown, the diameter of the flexible membrane isselected to ensure intimate contact of the flexible membrane with theartery 105 wall resulting in sufficient friction between the flexiblemembrane and the artery 105 wall to prevent embolization of device 1100.

In operation, device 1100 is located within the vasculature and thecompliant body 1110 is exposed to pulsatile pressure loads. Underpositive differential pressure, blood flowing in the blood vessel lumenof artery 105 presses against the compliant body 1110 and deforms theflexible membrane such that an equivalent volume of blood occupies thespace of the compliant volume. Under negative differential pressure, theflexible membrane returns to the original, undeformed position.

FIGS. 12 and 14 illustrate lateral and transverse cross sectional viewsof device 1300 according to one example. In the figures, device 1300includes compliant body 1310 with a central compliant body 1310 with acentral compliant volume 1315, the undeformed shape of which is definedby a flexible membrane designed for implantation between and within themuscular layers of a blood vessel, such as artery 105. The undeformedshape of the central compliant volume 1315 defined by a flexiblemembrane (in the form of a balloon) can assume many shapes including,but not limited to, cylindrical, ellipsoidal, polygonal cross-sectionswith mitered, concave, or convex features along the length of thecentral compliant volume 1315. In this embodiment, the flexible membraneis formed into an oblong cylindrical cross-sectional shape of a givenlength and central diameter cased on the central compliant volume 1315required for patient therapeutic requirements.

Device 1300 is secured to the vasculature with an anchor structure. Inthis example, device 1300 is positioned between muscular layers ofartery 105 ensuring intimate contact of the device 1300 with the artery105, thus resulting in sufficient friction between the flexible membraneand the lumen wall of artery 105 to prevent embolization of the device1300.

In operation, device 1300 located within the vasculature and is exposedto pulsatile pressure loads. Under positive differential pressure, bloodflowing in the vessel lumen of artery 105 presses against the bloodvessel lumen wall which in turn deforms the flexible membrane ofcompliant body 1310 such that an equivalent volume of blood occupies thespace of the compliant volume 1315. Under negative differentialpressure, the flexible membrane returns to the original, undeformedposition as defined insertion within the artery 105.

FIG. 13 depicts device 1300 located within void 95 of an interiorportion of the vessel wall. Void 95 can include a region between twolayers of a wall or within a single particular layer.

FIGS. 15 and 16 illustrate lateral cross sectional views of device 1500according to one example. In the example shown, device 1500 includesframe 1525 and diaphragm 1510 which cooperatively define a volume.Diaphragm 1510 is two stable modes and in one example, includes aflexible membrane. The flexible membrane can include a polymer or ametal (formed or stamped) to have bimodal configurations. In FIG. 15,diaphragm 1510 is illustrated to bow away from frame 1525 and extendinto the lumen of artery 105, thereby defining volume 1520A. In FIG. 16,diaphragm 1510 is illustrated to bow toward frame 1525 and away from thecenter of the lumen of artery 105, thereby defining volume 1520B. Volume1520B is less than volume 1520A and the air or gas therebetween can bevented to a larger region. In each of the two illustrated modes,diaphragm 1510 remains stable without undue influence.

Diaphragm 1510 can maintain one of two stable positions, namely, a stateof negative differential pressure (FIG. 15) and a state of positivedifferential pressure (FIG. 16).

Device 1500 includes a compliant body with a central compliant volume(1520A and 1520B) the undeformed shape of which is defined by adiaphragm 1510 which is configured to remain in either a concave mode ora convex mode with respect to the central compliant volume. Theundeformed shape of the central compliant volume defined by a diaphragm1510 can assume many shapes including, but not limited to, cylindrical,ellipsoidal, polygonal cross-sections with mitered, concave, or convexfeatures along the length of the central compliant volume. In theexample shown, the diaphragm 1510 is formed into a rectangularcross-sectional shape of a given length based on the central compliantvolume required for patient therapeutic requirements.

Device 1500 is secured to the vasculature using frame 1525. In thisexample, frame 1525 can be sutured to a blood vessel lumen wall (artery105) to prevent embolization of the device 1500. In one example, Device1500 is located within the blood vessel lumen and is held in a fixedposition by other structure to suspend device 1500 within the lumen.

In operation, device 1500 is located within the blood vessel lumen andis exposed to pulsatile pressure loads. Under positive differentialpressure, blood flowing in the blood vessel lumen presses against thediaphragm 1510 until such time that sufficient force is generated overthe area of the diaphragm 1510 that the buckling strength of theflexible membrane is exceeded and the diaphragm 1510 becomes convex withrespect to the central compliant volume. Under negative differentialpressure, the pressure contained within the central compliant volumepresses against the diaphragm 1510 until such time that sufficient forceis generated over the area of diaphragm 1510 that the buckling strengthof diaphragm 1510 is exceeded and diaphragm 1510 becomes concave withrespect to the central compliant volume whereby the diaphragm 1510 isreturned to the original, undeformed position.

FIG. 17 illustrates a portion of device 1700 according to one example.Device 1700 includes coaxial outer tube 1050 and inner tube 1704 havinga rolled, or everted end as shown at the top of the figure. Voice 1702between outer tube 1050 and inner tube 1704 provides a variable volumeregion. Inner tube 1704 is fabricated of an elastic or compliantmaterial. Void 1702 can be precharged with a predetermined pressure.Variations in fluid pressure in a fluid (such as blood) flowing throughthe lumen of inner tube 1704 will cause a change in the volume at void1702. A port in outer tube 1050 can be used to provide a precharge.

Device 1700 can be held in a fixed position within and artery or organusing interface 110 or other anchor structure.

ADDITIONAL NOTES

The energy storage device includes a membrane in one example. Themembrane provides a barrier to separate the blood (or other fluid) fromthe variable volume region. The membrane, in one example, is unstresseduntil the onset of pressure from the fluid. With the onset of pressure,the membrane is deflected from the initial position and takes on adistended mode. Modulation of pressure within the organ causes acorresponding modulation of the membrane position. The pressure in thevariable volume region will also modulate with change in position of themembrane.

In one example, the variable volume region is pressurized with apre-charge including a gas or a fluid. The pre-charge can be deliveredby a syringe, conversion of a liquid or solid substance to a gaseousphase (i.e., to off-gas a vapor), or by physical manipulation of themembrane. A variable volume region can have a pre-charge gas pressureselected based on various factors, including, for example, the bloodpressure or the stiffness of the membrane. In one example, thepre-charge is approximately 85% of the typical pressure in that organ.

In one example, the variable volume region can be pressurized afterimplantation. As such, a syringe or other means can be used to rechargethe energy storage device. Recharging can include directly injecting agas or fluid into the device. The injection can be delivered through aport on an exterior portion of the body (or through an arterial wall).

The variable volume region can be pressurized using a compressible gassuch as carbon dioxide, air, nitrogen, argon, helium, or other gas. Inone example, a large molecule gas is selected to reduce incidence of gasleak-down through the membrane. In one example, nitric oxide is selectedfor pressurizing the region. Nitric oxide gas leaked from a membrane andinto an artery can provide a therapeutic benefit to the tissue.

An example of the present subject matter can be implanted in thepulmonary artery. Other locations include placement in the right of leftmain pulmonary artery (MPA).

In one example, a device is located within a lumen of the artery andretained by a suspension or support structure. The device presents avolume that varies with pressure changes. In one example, the device iscoupled to an artery by a fluid-tight joint. The fluid tight joint canbe the result of endothelial cell development, by an adhesive, or otherstructure.

In one example, the energy storage device is passively operated based onpressure dynamics within the organ. As the pressure rises, energy isabsorbed and upon reduction in pressure, the energy is returned to thefluidic system. In one example, the energy storage device is activelymodulated. Active modulation can include a motor-driven piston ormembrane, a piezo-electric element, or other device that can bemodulated by an external energy source.

In one example, a plurality of compressible gaseous bubbles can bedelivered to the organ using a suitable manifold. The volume of thebubbles will modulate with changes in the pressure within the fluidicsystem. The delivery manifold can include an annular ring configured toemit bubbles into the organ.

A variety of energy storage devices can be used in the present system.In one example, such a device includes a sealed gas chamber above abodily fluid (such as blood). The gas chamber (or variable volumeregion) can be separated by a fluid-gas interface (without a barrier ormembrane) or can include a resilient membrane (diaphragm). The membranecan be in the form of a planar diaphragm or in the form of a bladder orballoon. The membrane can take a continuously variable position withinits range of freedom or can have any number of indexed modes. Forexample, a bi-stable membrane can have a first mode or a second modecorresponding to different volumes.

In one example, the energy storage device includes a gas-charged pistonor a spring-loaded piston. A gas-charged piston example includes afree-floating piston with a seal between the piston wall and thecylinder wall.

The energy storage device can be located internal to an organ (e.g.,wholly within the channel), external to the organ (e.g., coupled to anartery by a fluidic channel), or located partially internal andpartially external (e.g., in a wall of a vessel).

The surface area of the membrane, working deflection range of themembrane, and the pre-charge of the variable volume region can beselected to suit a particular application. In addition, multiple devicescan be used in series or in parallel configuration.

What is claimed is:
 1. A method of treating pulmonary hypertension, themethod comprising: anchoring a balloon within a pulmonary artery usingan interface coupled to the balloon such that the balloon is suspendedwithin a lumen of the pulmonary artery, wherein anchoring the ballooncomprises expanding the interface upon deployment to intimately contactan inner wall of the pulmonary artery, and wherein the ballooncompresses under a positive differential pressure in the pulmonaryartery such that blood flows between an outer surface of the balloon andthe inner wall of the pulmonary artery and expands under a negativedifferential pressure in the pulmonary artery such that blood flowsbetween the outer surface of the balloon and the inner wall of thepulmonary artery.
 2. The method of claim 1, wherein the interface has astent structure.
 3. The method of claim 1, wherein the interface isconfigured to enable endothelial cell development.
 4. The method ofclaim 1, wherein the balloon has a cylindrical shape.
 5. The method ofclaim 1, wherein anchoring the balloon comprises anchoring the balloonsuch that the interface is aligned with a longitudinal axis of theballoon.
 6. The method of claim 1, wherein the interface comprises ascaffold.
 7. The method of claim 1, wherein the interface comprises astent.
 8. The method of claim 1, wherein the interface comprises a metalmesh.
 9. The method of claim 1, wherein the interface comprises anon-metal mesh.
 10. The method of claim 1, wherein the ballooncompresses under the positive differential pressure such that anequivalent volume of blood occupies a space in the pulmonary arteryadjacent to the balloon.
 11. The method of claim 1, further comprisingpercutaneously installing the balloon using an introducer sheath. 12.The method of claim 11, further comprising percutaneously installing theballoon using an introducer guidewire.
 13. The method of claim 11,further comprising percutaneously installing the balloon using a needle.14. The method of claim 1, further comprising percutaneously installingthe balloon using a catheter.
 15. The method of claim 14, furthercomprising inflating the balloon using the catheter after installation.16. The method of claim 14, further comprising pressurizing the balloonusing the catheter after installation.